Manushka V. Vaidya1, Georgios Batsios1, Bei Zhang2, Ryan Brown2, Pavithra Viswanath1, Jan Paska2, Gerburg Wulf3, Aaron K. Grant4, Sabrina Ronen1, and Peder E.Z. Larson1
1Department of Radiology, University of California San Francisco, San Francisco, CA, United States, 2Center for Advanced Imaging Innovation and Research, and Center for Biomedical Imaging, New York University School of Medicine, New York, NY, United States, 3Department of Hematology-Oncology, Beth Israel Deaconess Medical Center, Boston, MA, United States, 4Department of Radiology, Beth Israel Deaconess Medical Center, Boston, MA, United States
Synopsis
In
this work, we constructed a 13C/31P surface coil for studying cancer metabolism
and bioenergetics in the brain. In a single scan session, hyperpolarized 13C-pyruvate
MRS and 31P MRS were carried out for a healthy rat brain. A commercial volume
proton coil was used for anatomical localization and B0 shimming. Results show good
detection of 13C labeled lactate, alanine, and bicarbonate in addition to ATP,
phosphocreatine, inorganic phosphate, phosphodiesters and phosphomonoesters
from 31P MRS. The coil enables obtaining complementary information within a scan session, thus reducing the number of
trials and minimizing biological variability for studies of metabolism and
bioenergetics.
PURPOSE:
Hyperpolarized Carbon (13C) MR
spectroscopy allows for in vivo measurements of metabolic conversion including 13C-pyruvate
to lactate, which is upregulated in brain cancer1. Phosphorus (31P)
MRS can be used to quantify ATP levels, allowing for complementary monitoring of
bioenergetics in tumors2. In this work, we constructed a dual tuned 13C/31P
coil for acquiring metabolism and energetics data to study cancer metabolism in
a single setting. As a first step towards this goal, we tested the coil on a
healthy rat brain.METHODS:
Experiments
were carried out on a 3 T animal MRI scanner (Biospec, Bruker, Billerica MA), and animal experiments were done
in accordance to the IACUC. The 13C/31P coil was
constructed such that the inner loop was tuned to 51.65 MHz (31P
frequency) and the outer loop was tuned to 32.09 MHz (13C frequency)
and matched to 50 Ohms when loaded with a saline phantom (Fig 1). An LCC trap
circuit3, consisting of an inductor and capacitor in parallel with
another capacitor, on the 13C coil was used to block currents at the
31P frequency to decouple the two channels of the multinuclear coil.
Tuning and matching were adjusted to obtain input power reflection less than 20
% at the respective center frequency inside the scanner. Either the 13C
or 31P channel was connected to the X-nucleus channel on the
scanner, while the other channel was terminated with a 50 Ohm load. Anatomical
localization and B0 shimming were carried out using a volume proton
(1H) coil (72 mm diameter, Bruker, MA). A coil file allowing for changing
between the 1H, 13C, and 31P channels was
constructed in ParaVision 6.0.1.
For adjusting center frequency and
system reference power for both channels, a spherical phantom (~200uL: 2M 1-13C-sodium
acetate, 2M diethyl(2-oxopropyl) phosphonate) was positioned at the center of
the coil (Fig 1). Diethyl(2-oxopropyl) phosphanate was specifically chosen so
that its phosphorus spectrum does not overlap with in vivo spectra. The system reference power for a 90 degree flip
angle was calculated by varying the transmit power of a series of single pulse
acquisitions. In order to
visualize the conversion of pyruvate to its downstream metabolic products in vivo, a bolus of hyperpolarized [1-13C]
pyruvate (Testbed, Oxford Instruments,
Oxfordshire UK) was administered to a healthy rat via tail vein. Slice
selective spectroscopic sequences were used to obtain 13C (flip
angle = 30 degrees, slice thickness = 10 mm, TR = 3s, repetitions = 64,
spectral points = 2048, spectral bandwidth = 6421.23 Hz) and 31P (flip
angle = 60 degrees, slice thickness = 15 mm, TR = 4s, averages = 256, spectral
points = 2048, spectral bandwidth = 6421.23 Hz) spectra through the brain
during a single scan session. Data were reconstructed in Mnova (MestReNova,
14.1.0). RESULTS:
The
Phosphorus spectrum in the brain showed clear Phosphocreatine and ATP peaks. In
addition, inorganic phosphate, phosphomonoesters, and phosphodiesters were also
observed (Fig 2). The summed (Fig 3) and first 14 time frames (Fig 4) of the
carbon spectra show the downstream metabolic products of 13C-pyruvate,
namely lactate, alanine, and bicarbonate. Slice positioning for both
phosphorus and carbon spectroscopic acquisitions are shown in the sagittal
anatomical slice obtained with the proton volume coil (Fig 2 and 3). DISCUSSION:
A
number of dual tuned coil arrays have been constructed to allow for proton
imaging for anatomical localization as well as X-nucleus imaging4,5.
This work demonstrates the implementation of a 13C/31P
coil in combination with an existing volume 1H coil to visualize
metabolism, energetics, and anatomy. A nested loop design for the 13C/31P
coil was chosen over a single loop design with two resonances in order to include
an LCC trap on the lower frequency coil, which has been shown to improve coil
sensitivity3. Future work on the coil includes the addition of cable
traps for both channels to minimize common mode currents on the cables, and implementation
of a switch to change between the 31P and 13C channels. CONCLUSIONS:
Non-invasive
visualization of 13C labeled pyruvate and its downstream products in
conjunction with 31P spectroscopy in the rat brain can be achieved using
a 13C/31P coil. Acknowledgements
This
work was supported by NIH Training Grant T32CA151022, American Cancer Society Research Scholar
Grant 18-005-01-CCE, NIH grant
P41 EB013598 and P41 EB017183. The
authors would like to thank Rohan Virgincar for discussions regarding creating
multinuclear coil files in ParaVision. References
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